Medical imaging device, tube voltage setting device, imaging control method, and recording medium storing imaging control program

ABSTRACT

A medical imaging device that includes: a press plate that presses a breast; an emitter that radiates radiation onto the breast; an acquisition section that acquires various information indicating a type of an acoustic matching member inserted between the press plate and the breast in cases in which ultrasound imaging of the breast is performed; and a setting section that sets a tube voltage of the emitter to a first tube voltage, in cases in which radiographic imaging of the breast is performed alone, and that sets the tube voltage of the emitter to a second tube voltage that is different from the first tube voltage, by employing the various information acquired by the acquisition section, in cases in which radiographic imaging and ultrasound imaging of the breast are performed consecutively with the acoustic matching member still inserted.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a continuation of U.S. Ser. No. 15/352,595, filed onNov. 16, 2016, which claims priority under 35 U.S.C. § 119 from JapanesePatent Application No. 2016-037685, filed on Feb. 29, 2016. The entirecontents of these applications are incorporated herein by reference.

FIELD

The present disclosure relates to a medical imaging device, a tubevoltage setting device, an imaging control method, and a recordingmedium storing an imaging control program.

BACKGROUND

There are cases in which breast examinations, diagnoses, etc. areperformed using both radiographic imaging and ultrasound imaging. Whenperforming radiographic imaging of a breast using an ordinarymammography machine, the breast of an examinee is placed in a pressedstate using a press plate. However, when performing ultrasound imagingof a breast using an ordinary ultrasound imaging device, imaging isperformed by an operator moving an ultrasound probe over the surface ofthe breast of an examinee. It is sometimes difficult, for example, toobserve the site of interest when comparing both images due todifferences in the pressed state of the breast of an examinee, and theimaging state etc. between when performing radiographic imaging and whenperforming ultrasound imaging. There is accordingly a desire for amedical imaging device capable of performing both radiographic imagingand ultrasound imaging, and, for example, technology is described inJapanese Patent Application Laid-Open (JP-A) Nos. 2009-082399 and2005-270677.

In the technology described in JP-A Nos. 2009-082399 and 2005-270677, anultrasound image and a radiographic image are acquired in which thepressed state of the breast of an examinee, and the imaging state, etc.have been made the same, by performing radiographic imaging andultrasound imaging in a pressed state of the breast of a single examineeusing a single medical imaging device. This facilitates observation ofthe site of interest and so on in a comparison of the radiographic imageand the ultrasound image of the same breast.

Generally, when performing ultrasound imaging, in order to reducednon-uniformity in the impedance of ultrasound waves, an acousticmatching member is inserted between the ultrasound probe and the breast.When performing radiographic imaging in a state in which an acousticmatching member has been inserted, radiation that has passed through theacoustic matching member is incident to the breast. Thus, for example,the characteristics of the radiation incident to the breast is sometimesdifferent to that of radiation incident to the breast without passingthrough the acoustic matching member.

SUMMARY

A medical imaging device of the present disclosure includes a pressplate that presses a breast, an emitter that radiates radiation onto thebreast, an acquisition section that acquires various informationindicating a type of an acoustic matching member inserted between thepress plate and the breast in cases in which ultrasound imaging of thebreast is performed, and a setting section. The setting section sets atube voltage of the emitter to a first tube voltage in cases in whichradiographic imaging of the breast is performed alone, and that sets thetube voltage of the emitter to a second tube voltage different from thefirst tube voltage by employing the various information acquired by theacquisition section in cases in which radiographic imaging andultrasound imaging of the breast are performed consecutively with theacoustic matching member still inserted.

BRIEF DESCRIPTION OF DRAWINGS

FIG. 1 is a side view illustrating the external appearance of an imagingsection of a medical imaging device of a first exemplary embodiment.

FIG. 2 is a block diagram illustrating a configuration of a medicalimaging device of the first exemplary embodiment.

FIG. 3 is a diagram to explain performing radiographic imaging using amedical imaging device of the first exemplary embodiment in a state inwhich an acoustic matching member has been provided.

FIG. 4 is a diagram to explain performing radiographic imaging using amedical imaging device of the first exemplary embodiment in a state inwhich an acoustic matching member has not been provided.

FIG. 5 is a flowchart illustrating an imaging operation in a consecutiveimaging mode in which radiographic imaging and ultrasound imaging areperformed consecutively by a medical imaging device of the firstexemplary embodiment.

FIG. 6 is a diagram to explain performing ultrasound imaging using amedical imaging device of the first exemplary embodiment.

FIG. 7 is a flowchart illustrating a flow of radiographic imagingprocessing by a medical imaging device of the first exemplaryembodiment.

FIG. 8 is diagram illustrating an example of a tube voltage changetable.

FIG. 9 is a diagram illustrating an example of a dose change table.

FIG. 10 is diagram to explain an acoustic matching member having amarker.

FIG. 11 is a flowchart illustrating an imaging operation in aconsecutive imaging mode in which radiographic imaging and ultrasoundimaging are performed consecutively by a medical imaging device of asecond exemplary embodiment.

FIG. 12 is a flowchart illustrating a flow of radiographic imagingprocessing by a medical imaging device of the second exemplaryembodiment.

FIG. 13 is diagram to explain a radiographic image obtained by a preshotincluding an image of a marker.

FIG. 14 is a block diagram illustrating a configuration of a medicalimaging device equipped with a camera for imaging a marker.

FIG. 15 is a flowchart illustrating an imaging operation in aconsecutive imaging mode in which radiographic imaging and ultrasoundimaging are performed consecutively by the medical imaging deviceillustrated in FIG. 4.

FIG. 16 is a block diagram illustrating a configuration of a tubevoltage setting device and a medical imaging device.

DETAILED DESCRIPTION OF THE INVENTION

Detailed explanation follows regarding exemplary embodiments of thepresent disclosure, with reference to the drawings. Note that thepresent disclosure is not limited to the present exemplary embodiments.

First Exemplary Embodiment

First, explanation follows regarding a configuration of a medicalimaging device according to the present exemplary embodiment, withreference to FIG. 1.

A medical imaging device 10 of the present exemplary embodiment combinesfunctionality of a radiographic mammography machine that performsradiographic imaging by radiating radiation R onto a breast of a subjectand detecting the radiation R that has passed through the breast, andfunctionality of a ultrasound imaging device that performs ultrasoundimaging by transmitting ultrasound waves through the breast of asubject, and receiving an ultrasound echo reflected by the interior ofthe breast.

As illustrated in FIG. 1, the medical imaging device 10 of the presentexemplary embodiment includes an arm 20, a stand 22, and a shaft 24. Thestand 22 holds the arm 20 so that the arm 20 is movable in the up-downdirection (the Z axis direction). The shaft 24 connects the arm 20 tothe stand 22. The arm 20 is able to rotate relative to the stand 22about a rotation axis of the shaft 24.

A radiation emitter 25, an imaging table 31, a press plate 32, a pressplate moving mechanism 34, an ultrasound probe 36, and a probe movingmechanism 38 are provided to the arm 20.

The radiation emitter 25 includes a radiation tube 26, a filter 28, anda high voltage generator 29. The radiation tube 26 generates radiation Rby application of a tube voltage. The filter 28 is formed from amaterial such as molybdenum (MO) or rhodium (Rh), and selectively allowsdesired wavelength components, from out of plural wavelength componentscontained in the radiation R generated by the radiation tube 26, to passthrough.

In order to perform imaging, the breast of an examinee is positioned onthe imaging table 31. From the perspectives of transmissivity toradiation R and strength, the imaging table 31 and the like that thebreast of the examinee contacts are formed from a carbon composite, forexample. A radiation detector 30 is disposed inside the imaging table 31for detecting radiation R that has passed through the breast and theimaging table 31. Radiographic imaging is generated based on theradiation R detected by the radiation detector 30. There are noparticular limitations to the type of the radiation detector 30 of thepresent exemplary embodiment, and, for example, an indirect conversiontype of radiation detector may be employed that converts radiation Rinto light and then converts the converted light into charge, or adirect conversion type of radiation detector may be employed thatconverts the radiation R directly into charge.

The press plate 32 is moved in the up-down direction (the Z axisdirection) by the press plate moving mechanism 34, and presses thebreast of the examinee against the imaging table 31. The press plate 32is preferably optically transparent in order to confirm positioning andthe pressed state during pressing of the breast, and is formed from amaterial having excellent transmissivity to the radiation R in order toreadily transmit the radiation R emitted from the radiation emitter 25.The press plate 32 is also preferably formed from a material thatreadily propagates ultrasound waves transmitted from the ultrasoundprobe 36. Examples of materials that may be employed for the press plate32 include resins such as polymethylpentene, polycarbonate, acrylic, andpolyethylene terephthalate. Polymethylpentene is particularlyappropriately employed as the material of the press plate 32 due tohaving a low rigidity, excellent extensibility and flexibility, and alsohaving appropriate values of sound impedance, which influences thereflectivity of ultrasound waves, and attenuation coefficient, whichinfluences ultrasound wave attenuation.

The ultrasound probe 36 is moved along the upper face of the press plate32 (the face on the opposite side to the side where the breast of theexaminee is disposed) by the probe moving mechanism 38, and acquires anultrasound image of the breast by scanning the breast with ultrasoundwaves. The ultrasound probe 36 includes plural ultrasound transducersarrayed in one dimension or in two dimensions. Each of the ultrasoundtransducers transmits ultrasound waves according to a drive signalapplied thereto, and outputs a reception signal by receiving anultrasound echo.

Each of the plural ultrasound transducers is, for example, configured bya vibration element having electrodes formed on both ends of a materialhaving piezoelectric properties (a piezoelectric body), such as apiezoelectric ceramic as typified by Pb (lead) zirconate titanate (PZT),or a polymer piezoelectric element as typified by polyvinylidenedifluoride (PVDF). The piezoelectric body expands and contracts when adrive signal of a pulse shape or a continuous wave is transmitted to theelectrodes of the vibration element and a voltage is applied thereto.Pulse shaped or continuous wave ultrasound waves are generated from therespective vibration elements by the expansion and contraction, and anultrasound wave beam is formed by these ultrasound waves combining. Therespective vibration elements also expand and contract on receivingpropagating ultrasound waves, and generate an electrical signal. Theseelectrical signals are output as ultrasound reception signals, and areinput to a controller 40 (see FIG. 2) through a cable.

In order to perform ultrasound imaging, the ultrasound probe 36 is movedalong the upper face of the press plate 32 in a state in which the upperface of the press plate 32 has been coated in an acoustic matchingmember such as an echo jelly (described in detail below, see FIG. 6). Inthe medical imaging device 10 of the present exemplary embodiment,ultrasound imaging is performed automatically, without an operatormoving the ultrasound probe 36, by the controller 40 (see FIG. 2) movingthe ultrasound probe 36 using the probe moving mechanism 38. Note thatthere is no limitation to the present exemplary embodiment, andultrasound imaging may be performed by an operator moving the ultrasoundprobe 36.

As illustrated in FIG. 2, the medical imaging device 10 of the presentexemplary embodiment also includes a pressure sensor 33, a positionsensor 37, the controller 40, a storage unit 42, an operation panel 44,and an interface (I/F) 46. The radiation emitter 25, the radiationdetector 30, the pressure sensor 33, the press plate moving mechanism34, the ultrasound probe 36, the position sensor 37, the probe movingmechanism 38, the controller 40, the storage unit 42, the operationpanel 44, and the interface (I/F) 46 are connected together by a bus 49,such as a system bus or a control bus, so as to be capable of exchangingvarious signals with each other.

The controller 40 includes a central processing unit (CPU) 40A, readonly memory (ROM) 40B, and random access memory (RAM) 40C. Variousprograms, etc. to be executed by the CPU 40A are pre-stored in the ROM40B. The RANI 40C temporarily stores various data.

The pressure sensor 33 detects pressure applied to the press plate 32.The position sensor 37 is internally installed in the ultrasound probe36, and detects the position of the ultrasound probe 36 (the position onthe surface of the press plate 32).

The controller 40 controls the overall operation of the medical imagingdevice 10. The controller 40 of the present exemplary embodimentcontrols the radiation emitter 25, the radiation detector 30, and thepress plate moving mechanism 34 to perform radiographic imaging. Basedon the detection results of the pressure sensor 33, the controller 40uses the press plate moving mechanism 34 to move the press plate 32 andpress the breast against the imaging table 31. The controller 40 causesthe radiation R to be emitted from the radiation tube 26 by theradiation emitter 25. The transmissivity to the radiation R isdetermined by the tube voltage applied between the cathode and the anodeof the radiation tube 26. The amount of radiation R generated, namely,the dose of the radiation R radiated onto the breast, is determined bythe integral value of the tube current flowing between the cathode andthe anode of the radiation tube 26 with respect to time (also sometimesreferred to as the mAs value). Thus the controller 40 adjusts theimaging conditions, such as the tube voltage and the tube current, suchthat the radiation R is emitted from the radiation emitter 25 byapplying a high voltage generated by the high voltage generator 29 tothe radiation tube 26. The controller 40 performs radiographic imagingby using the radiation detector 30 to detect the radiation R that haspassed through the breast.

In order to perform ultrasound imaging, the controller 40 of the presentexemplary embodiment controls the ultrasound probe 36 and the probemoving mechanism 38. The controller 40 acquires the position of theultrasound probe 36 based on the detection results of the positionsensor 37, and uses the probe moving mechanism 38 to move the ultrasoundprobe 36. The controller 40 performs ultrasound imaging by transmittingand receiving ultrasound waves, while moving the ultrasound probe 36with the probe moving mechanism 38.

The respective image data of the radiographic images and the ultrasoundimages obtained by imaging, and/or various other data, is stored in thestorage unit 42. Examples of the storage unit 42 include a hard diskdrive (HDD) and a solid state drive (SSD). A tube voltage change table42A and a dose change table 42B (see FIG. 8 and FIG. 9, both of whichare described in detail below) are stored in the storage unit 42 of thepresent exemplary embodiment.

The operation panel 44 receives instructions relating to imaging (suchas instructions to press the breast with the press plate 32) from anoperator performing radiographic imaging and ultrasound imaging. Theoperation panel 44 is, for example, provided on the arm 20 of themedical imaging device 10. The operation panel 44 may be a touch panel.

The I/F 46 performs communication of various information with anexternal system (such as a radiology information system (RIS)) and/orwith a console using wireless communication or wired communication. Inthe medical imaging device 10 of the present exemplary embodiment,acquired radiographic images and/or ultrasound images are transmittedfrom the I/F 46 to a console and/or to a reading device (such as aviewer).

Next, explanation follows regarding performing radiographic imaging andultrasound imaging in the medical imaging device 10 of the presentexemplary embodiment.

The medical imaging device 10 of the present exemplary embodiment has animaging mode to perform consecutive radiographic imaging and ultrasoundimaging (referred to below as a “consecutive imaging mode”), and animaging mode to perform either one from out of radiographic imaging orultrasound imaging. Explanation follows regarding execution by themedical imaging device 10 of the consecutive imaging mode.

Generally, when performing ultrasound imaging of a breast in a statepressed by the press plate 32, an acoustic matching member is insertedbetween the press plate 32 and the breast in order to reducenon-uniformity in the impedance to ultrasound waves at the contact planebetween the press plate 32 and the breast. In cases in which theconsecutive imaging mode is executed in the medical imaging device 10 ofthe present exemplary embodiment, in order to consecutively perform bothradiographic imaging and ultrasound imaging in a state in which thepress plate 32 presses the breast all the time until radiographicimaging and ultrasound imaging have been completed, without releasingthe pressing of the breast, an acoustic matching member 50 that is notrequired to perform radiographic imaging is inserted between the pressplate 32 and the breast N even during radiographic imaging, as in theexample illustrated in FIG. 3.

However, as illustrated in the example in FIG. 4, radiographic imagingis performed without providing the acoustic matching member 50 whenradiographic imaging (mammography) of a breast is normally performed. Inthe medical imaging device 10 of the present exemplary embodiment too,the acoustic matching member 50 is not inserted when in an imaging modethat performs radiographic imaging of a breast alone, without performingultrasound imaging.

The acoustic matching member 50 inserted between the press plate 32 andthe breast N in the medical imaging device 10 of the present exemplaryembodiment is made of a material that exhibits both good compatibilityto a biological object (the breast N in the present exemplaryembodiment) and transmissivity to ultrasound waves. The acousticmatching member 50 is preferably formed from a material that isphysically strong while being soft, that has good transmissivity toultrasound waves, and that is also capable of withstanding sterilizationtreatment. Examples of materials that may be employed as the acousticmatching member 50 include non-water containing gel substances such asurethane rubbers and silicone rubbers, and water containing polymer gelssuch as polyvinyl alcohols and polyethylene oxides. Note that in orderto retain shape, what is referred to as a gel pad, in which the surfaceof the acoustic matching member 50 is covered by a silicone rubber orthe like, is employed as the acoustic matching member 50 in the medicalimaging device 10 of the present exemplary embodiment.

The characteristics of the radiation R change due to passing throughsuch the acoustic matching member 50. Thus, the characteristics of theradiation R incident to the breast N is different in cases in which theacoustic matching member 50 has been inserted between the press plate 32and the breast N to in cases in which the acoustic matching member 50has not been inserted. For example, in cases in which the radiation R isX-rays, what is referred to as beam hardening occurs in which the energyis shifted to the high energy side by passing through the acousticmatching member 50, and the radiation quality of the radiation Rchanges. The contrast is decreased of radiographic images imaged whenthe radiation R has been shifted to the high energy side in this manner.Moreover, for example, dose is reduced of the radiation R incident tothe breast N due to the radiation R being absorbed by the acousticmatching member 50.

Note that changes to the radiation quality of the radiation R depend inparticular on the thickness of the acoustic matching member 50 at theportion where the radiation R passes through, and there is a greaterchange in the radiation quality of the radiation R the greater thethickness of the portion of the acoustic matching member 50 passedthrough. Hence, in the medical imaging device 10 of the presentexemplary embodiment, as an example, the type of the acoustic matchingmember 50 is determined according to the thickness of the portion of theacoustic matching member 50 passed through.

The controller 40 of the medical imaging device 10 of the presentexemplary embodiment accordingly controls such that the characteristicsof the radiation R incident to the breast N (more precisely theradiation quality and the dose) is equivalent, or substantiallyequivalent, in cases in which radiographic imaging is performed in astate in which the acoustic matching member 50 has been inserted betweenthe press plate 32 and the breast N, as illustrated in the example inFIG. 3, and in cases in which radiographic imaging is performed in astate in which the acoustic matching member 50 has not been insertedbetween the press plate 32 and the breast N, as illustrated in theexample in FIG. 4.

FIG. 5 illustrates the overall flow of a chain of an imaging operationin cases in which an operator employs the medical imaging device 10 ofthe present exemplary embodiment to perform radiographic imaging andultrasound imaging in the consecutive imaging mode.

First, at step S100, the operator inputs information indicating the typeof the acoustic matching member 50 (details are described later)inserted between the breast and the press plate 32 using the operationpanel 44 and/or an external device or the like.

At the next step S102, the operator positions the breast N of theexaminee on the imaging table 31.

Then, at the next step S104, the medical imaging device 10 presses thebreast N of the examinee using the press plate 32 in a state in whichthe acoustic matching member 50 has been inserted onto the upper surfaceof the breast N (the surface on the side of the press plate 32). Moreprecisely, at the end of positioning, the operator inputs an instructionthrough the operation panel 44 to move the press plate 32. Thecontroller 40 presses the breast N in a state sandwiching the acousticmatching member 50 by moving the press plate 32 in the direction toapproach the imaging table 31 using the press plate moving mechanism 34according to the instruction input by the operator.

Note that there are no particular limitations to the method of insertingthe acoustic matching member 50 in cases in which the breast N ispressed by the press plate 32. In cases in which it is possible toattach the acoustic matching member 50 to the face of the press plate 32on the breast side, the breast N may be pressed by the press plate 32 ina state in which the acoustic matching member 50 has been attached tothe press plate 32. The breast N may also be pressed by the press plate32 in a state in which the operator has placed the acoustic matchingmember 50 on the breast N.

Then, at step S106, the medical imaging device 10 performs radiographicimaging of the breast N by the controller 40 executing radiographicimaging processing (see FIG. 7, details given later). Note that in casesin which radiographic imaging is performed, the controller 40 uses theprobe moving mechanism 38 to retract the ultrasound probe 36 to outsideof the radiographic image detection region detected by the radiationdetector 30.

At the end of radiographic imaging, at the next step S108, the operatorcoats echo jelly 52 onto the upper face of the press plate 32 (the faceon the opposite side to the face where the breast N is disposed), asillustrated in the example in FIG. 6. The echo jelly 52 is also anacoustic matching member. As the echo jelly 52, a low viscosityobstetric gel having, for example, components of distilled water, amoisturizer (at least one of propylene or glycol), a macromoleculepolymer, soluble lanolin, a colorant, a perfume, and a preservative (atleast one of propylparaben or antiseptic methylparaben), having aneutral pH value in the range of from 6.5 to 7.0, and viscosity from25000 CPS to 45000 CPS is suitably employed.

Then, at step S110, the medical imaging device 10 performs ultrasoundimaging of the breast N. When doing so, as described above, thecontroller 40 uses the probe moving mechanism 38 to move the ultrasoundprobe 36 so as to move along the surface of the press plate 32 coated inthe echo jelly 52 (the surface facing the radiation tube 26), whiledetecting the position of the ultrasound probe 36 using the positionsensor 37. The controller 40 then performs ultrasound imaging bytransmitting ultrasound waves from the ultrasound probe 36 through thebreast N, and receiving an ultrasound echo reflected by the interior ofthe breast N.

At the end of ultrasound imaging, at the next step S112, the medicalimaging device 10 releases pressing of the breast N by the press plate32. More precisely, the operator inputs an instruction through theoperation panel 44 to move the press plate 32 (inputs an instruction torelease pressing). The controller 40 releases pressing of the breast Nby moving the press plate 32 in the direction away from the imagingtable 31 using the press plate moving mechanism 34 according to theinstruction input by the operator.

When pressing of the breast N has been released in this manner, theimaging operation in the consecutive imaging mode is ended.

Next, explanation follows regarding radiographic imaging of the presentexemplary embodiment executed at the above step S106, with reference toFIG. 7. FIG. 7 is a flowchart of an example of radiographic imagingprocessing executed by the controller 40 at step S106.

At step S200, the controller 40 acquires an imaging menu. Information,such as information related to the imaging conditions, the examinee, andthe breast N, is contained in the imaging menu. For example, thecontroller 40 may acquire the imaging menu from an external system orthe like through the I/F 46, or may acquire the imaging menu input bythe operator through the operation panel 44.

At the next step S202, the controller 40 determines whether or not toemit radiation R. In the medical imaging device 10 of the presentexemplary embodiment, the operator instructs radiation from a deviceexternal to the medical imaging device 10 (for example, from a console,and/or from a device provided with a dedicated switch to instructradiation of the radiation R) or the like. On receipt of a radiationinstruction from such an external device or the like, the controller 40determines (determines in the affirmative) to emit the radiation R. Incases in which negative determination is made here, a standby state isadopted, and when affirmative determination is made, processingtransitions to step S204.

At step S204, the controller 40 performs a preshot by emitting theradiation R from the radiation emitter 25. In order to obtain aradiographic image with an appropriate contrast, in the preshot of thepresent exemplary embodiment the radiation R is radiated for the purposeof estimating an appropriate integral of tube current over time Q (dose)of the radiation R to be radiated from the radiation emitter 25 onto thebreast N during the main shot. Main shot refers to the radiation of theradiation R onto the breast N for the purpose of acquiring radiographicimages for use in examination and diagnosis.

At the next step S206, the controller 40 determines the tube voltage forthe main shot based on the tube voltage change table 42A. As describedabove, the radiation quality of the radiation R changes due to passingthrough the acoustic matching member 50. The radiation quality of theradiation R changes according to the tube voltage. Hence, by adjustingthe tube voltage in the medical imaging device 10 of the presentexemplary embodiment, the radiation quality in cases in which theradiation R is incident to the breast N after passing through theacoustic matching member 50 is made equivalent to the radiation qualityin cases in which the radiation R is incident to the breast N after notpassing through the acoustic matching member 50. In the presentexemplary embodiment, reference to “equivalent” means within a rangethat can be taken as being equivalent, including measurement errors anda permissible range.

Namely, by making the tube voltage different in the medical imagingdevice 10 of the present exemplary embodiment, the radiation quality ofthe radiation R for imaging the same breast N is made equivalent incases in which radiographic imaging is performed in the consecutiveimaging mode, and the imaging mode that performs radiographic imagingalone. In the present exemplary embodiment, the tube voltage whenperforming radiographic imaging alone corresponds to a first tubevoltage, and the tube voltage when radiographic imaging is performed inthe consecutive imaging mode corresponds to a second tube voltage.

More precisely, in the medical imaging device 10 of the presentexemplary embodiment, the half value layer of the radiation R is madeequivalent by making the tube voltages different. Thus, in the presentexemplary embodiment, for example, the tube voltage in cases in whichradiographic imaging is performed alone is taken as the tube voltageprior to changing, the tube voltage in cases in which radiographicimaging is performed in the consecutive imaging mode is taken as thetube voltage after changing, and correspondence relationships areobtained in advance between the tube voltage prior to changing, the typeof acoustic matching member 50, and the tube voltage after changinggiving an equivalent half value layer of the radiation R. FIG. 8illustrates the tube voltage change table 42A that is an example ofcorrespondence relationships between tube voltage prior to change andtube voltage after changing giving an equivalent half value layer of theradiation R. Although in the present exemplary embodiment the tubevoltage change table 42A is stored in the storage unit 42 in advance, asdescribed above, the appropriate tube voltage change table 42A may beacquired from an external device or the like in cases in which theconsecutive imaging mode is executed.

As illustrated in FIG. 8, the tube voltage change table 42A indicatescorrespondence relationships between device specific tube voltages priorto changing, the model number (an example of type) of the acousticmatching member 50, and the tube voltage after changing, that give anequivalent half value layer. Note that although, for ease ofexplanation, the tube voltage change table 42A illustrated in FIG. 8lists “device specific half value layers”, the “device specific halfvalue layers” do not need to be included in the tube voltage changetable 42A. Note that although in the tube voltage change table 42Aillustrated in FIG. 8, the tube voltage after changing is associatedwith the tube voltage prior to changing and the type (model number) ofthe acoustic matching member 50, rather than the tube voltage afterchanging itself, a correction value to correct the tube voltage prior tochanging may be associated therewith.

More precisely, the controller 40 acquires the type of the acousticmatching member 50 input by the operator at step S100 in the flow of theimaging operation in the consecutive imaging mode described above (seeFIG. 5), and acquires the tube voltage (the tube voltage prior tochanging) from the imaging menu acquired at step S200. Then, at stepS206, the controller 40 determines the tube voltage corresponding to theacquired type of the acoustic matching member 50 and the acquired tubevoltage prior to changing, based on the tube voltage change table 42A,and sets the determined tube voltage in the radiation emitter 25.

At the next step S208, the controller 40 determines the dose of theradiation R based on the results of the preshot and the dose changetable 42B. As described above, the dose of the radiation R is changed bypassing through the acoustic matching member 50. Hence, by adjusting thedose in the medical imaging device 10 of the present exemplaryembodiment, the dose (mAs value) of the radiation R in cases in whichthe radiation R is incident to the breast N after passing through theacoustic matching member 50 is equivalent to the dose of the radiation Rin cases in which the radiation R is incident to the breast N after notpassing through the acoustic matching member 50. Note that there are noparticular limitations to the method by which the dose is adjusted, aslong as at least one out of the tube current or the radiation time isadjusted. Note that from the perspective of suppressing the time thebreast N of the examinee is pressed, the dose is preferably adjusted byadjusting the tube current.

More precisely, as an example of the present exemplary embodiment,correspondence relationships between the tube voltage after changing,the type of the acoustic matching member 50, and a dose correction valueare obtained in advance. FIG. 9 illustrates the dose change table 42Bthat is an example of correspondence relationships between the tubevoltage after changing, the type of the acoustic matching member 50, anda dose correction value. In the present exemplary embodiment, asdescribed above, the dose change table 42B is pre-stored in the storageunit 42; however, the dose change table 42B may be acquired from anexternal device or the like when the consecutive imaging mode isexecuted.

As illustrated in FIG. 9, the dose change table 42B indicatescorrespondence relationships between the tube voltage after changing,the model number (an example of type) of the acoustic matching member50, and a dose correction coefficient (an example of a dose correctionvalue). Note that the dose correction coefficient in the dose changetable 42B of the present exemplary embodiment is a reciprocal of thetransmissivity of the radiation R through the acoustic matching member50. Note that although in the dose change table 42B illustrated in FIG.9, the dose correction coefficient is associated with tube voltage afterchanging and the type (model number) of the acoustic matching member 50,rather than the dose correction coefficient, the tube voltage itselfafter changing may be associated therewith.

More precisely, the controller 40 takes the tube voltage determined atstep S206 as the tube voltage after changing and determines the dosecorrection coefficient corresponding to the tube voltage after changingand the type of the acoustic matching member 50 based on the dose changetable 42B. The dose of the main shot is determined by correcting thedose derived from the preshot results with the determined dosecorrection coefficient, and the determined corrected dose is set in theradiation emitter 25.

At the next step S210, the controller 40 performs the main shot bycausing the radiation R to be emitted from the radiation emitter 25.More precisely, the controller 40 performs the main shot by causingradiation to be emitted from the radiation emitter 25 according to thetube voltage determined at step S206 and the dose determined at stepS208. Then, after radiographic imaging of the breast N has beenperformed using the radiation detector 30, the controller 40 ends thepresent radiographic imaging processing.

Second Exemplary Embodiment

Next, explanation follows regarding a second exemplary embodiment. Partssimilar to those of a radiographic imaging system 1 according to thefirst exemplary embodiment are appended with the same referencenumerals, and detailed explanation thereof is omitted.

Configuration of a radiographic imaging system 1 is similar to that ofthe radiographic imaging system 1 of the first exemplary embodiment (seeFIG. 1 and FIG. 2) and so explanation thereof is omitted.

In the present exemplary embodiment, the method of acquiring the type ofthe acoustic matching member 50 differs to that of the radiographicimaging system 1. In the first exemplary embodiment, the operator inputsthe type of the acoustic matching member 50, as illustrated by step S100in the flow of an imaging operation in the consecutive imaging mode (seeFIG. 5), and the controller 40 acquires the input type of the acousticmatching member 50. However, in the medical imaging device 10 of thepresent exemplary embodiment, the controller 40 acquires the type of theacoustic matching member 50 automatically without operator input.

The acoustic matching member 50 of the present exemplary embodimentincludes a marker indicating information to identify the type of theacoustic matching member 50. In the example illustrated in FIG. 10, theacoustic matching member 50 includes a marker 60 indicating the type(model number) of the acoustic matching member 50 at one location fromout of the corners (corner portions) of the acoustic matching member 50.There are no particular limitations to the substance and so on of themarker 60, and it is sufficient that the substance of the marker 60 is asubstance recognizably imaged in radiographic imaging, and is asubstance having a different transmissivity to the acoustic matchingmember 50 and the radiation R. The position where the marker 60 isdisposed at one location from the four corners of the acoustic matchingmember 50 is not limited to that of the example illustrated in FIG. 10,and is not particularly limited; however, it is preferably a positionnot overlapping with the image of the breast N.

The controller 40 of the medical imaging device 10 in the presentexemplary embodiment acquires the type of the acoustic matching member50 based on the distinguishing results from distinguishing the image ofthe marker 60 in the radiographic image obtained by the preshot.

Hence, as illustrated in FIG. 11, the imaging operation in theconsecutive imaging mode in the medical imaging device 10 of the presentexemplary embodiment is different to the imaging operation of theconsecutive imaging mode in the medical imaging device 10 of the firstexemplary embodiment (see FIG. 5), in the point that step S100 is notexecuted.

Moreover, as illustrated in FIG. 11, in the imaging operation in theconsecutive imaging mode of the medical imaging device 10 of the presentexemplary embodiment, step S106A is executed in place of step S106 ofthe imaging operation of the consecutive imaging mode of the firstexemplary embodiment (see FIG. 5).

Explanation follows regarding performing radiographic imaging in thepresent exemplary embodiment by executing step S106A of the consecutiveimaging mode using the medical imaging device 10 of the presentexemplary embodiment, with reference to FIG. 12. FIG. 12 is a flowchartof an example of radiographic imaging processing executed by thecontroller 40 at step S106A.

The radiographic imaging processing of the present exemplary embodimentdiffers from that of the first exemplary embodiment in the point thatthe processing of steps S205A to S205C is executed between steps S204and step S206 in the radiographic imaging processing of the firstexemplary embodiment (see FIG. 7).

As illustrated in the example in FIG. 13, a radiographic image 70obtained by the preshot executed at step S204 contains a breast N image72, and a marker image 73.

Thus at step S205A, the controller 40 detects the marker image 73 in theradiographic image 70 obtained by the preshot. Note that the method ofdetecting the marker image 73 is not particularly limited, and themarker may be detected by performing image analysis or the like.

At the next step S205B, the controller 40 obtains information of themarker 60 based on the detected marker image 73. Then at the next stepS205C, the controller 40 acquires the type of the acoustic matchingmember 50 by identifying the type of the acoustic matching member 50based on the acquired information of the marker 60. The method ofacquiring the information of the marker 60 from the marker image 73, andthe method of identifying the type of the acoustic matching member 50based on the information of the marker 60, are not particularly limited.For example, the type of the acoustic matching member 50 may beidentified based on information stored in the storage unit 42 indicatingcorrespondence relationships between the information of the marker 60and the type of each acoustic matching member 50.

Thus, in the medical imaging device 10 of the present exemplaryembodiment, imaging is performed in the consecutive imaging mode usingthe acoustic matching member 50 having the marker 60 indicatinginformation to identify the type of the acoustic matching member 50. Thecontroller 40 then detects the marker image 73 in the radiographic image70 obtained by the preshot, acquires the information of the marker 60,and acquires the type of the acoustic matching member 50 based on theinformation of the marker 60.

Thereby, according to the medical imaging device 10 of the presentexemplary embodiment, due to being able to automatically acquire theappropriate type of the acoustic matching member 50, the operator doesnot need to input the type of the acoustic matching member 50.

Thereby, according to the medical imaging device 10 of the presentexemplary embodiment, due to being able to automatically acquire theappropriate type of the acoustic matching member 50, there is no needfor the operator to input the type of the acoustic matching member 50.

Note that preferably the controller 40 gives a warning to the operatorin the following cases. Namely, in cases in which it has not beenpossible for the controller 40 to detect the marker image 73 from theradiographic image 70 obtained by the preshot, in cases in which it hasnot been possible to acquire the information of the marker 60 eventhough the marker image 73 has been detected, and in cases in whichthere was no type of acoustic matching member 50 associated with theacquired marker 60 information, for example, such as by displaying thesituation on the operation panel 44.

Note that although in the medical imaging device 10 of the presentexemplary embodiment, the radiographic image 70 from imaging the marker60 on the acoustic matching member 50 in the preshot is employed inorder for the controller 40 to automatically acquire the type of theacoustic matching member 50, there is no limitation thereto, and animage obtained by another method may be employed therefor.

For example, an image of the breast N may be imaged without emittingradiation R from the radiation emitter 25, and images imaged by a normalcamera (an ordinary digital camera) may be employed. In such cases, themedical imaging device 10 further includes a camera 39 as an imagingsection for imaging the marker 60 on the acoustic matching member 50, asillustrated in FIG. 14. Moreover, as an example, operation of theconsecutive imaging mode is executed in the medical imaging device 10 asillustrated in FIG. 15. The imaging operation of the consecutive imagingmode illustrated in FIG. 15 differs from the imaging operation of theconsecutive imaging mode in the medical imaging device 10 of the presentexemplary embodiment (see FIG. 5) in the point that performing of stepsS105A to S105D is executed between step S104 and step S106.

At step S105A as illustrated in FIG. 15, the controller 40 images themarker 60 on the acoustic matching member 50 using the camera 39. Theimaging performed here does not need to image the breast N, as long asthe marker 60 is imaged. At the next step S105B, the controller 40detects the image of the marker in the image obtained using the camera39. Note that there is no particular limitation to the method ofdetecting the image of the marker, and detection may be performed byimage analysis or the like. At the next step S105C, the controller 40acquires information of the marker 60 based on the detected markerimage. Then at the next step S105D, the controller 40 acquires the typeof the acoustic matching member 50 by identifying the type of theacoustic matching member 50 based on the acquired information of themarker 60. There are no particular limitations to the method ofacquiring the information of the marker 60 from the marker image, or tothe method of identifying the type of the acoustic matching member 50based on the information of the marker 60, and they may be similar tocases in which the radiographic image 70 obtained by the preshot isemployed.

Thus, according to the imaging operation of the consecutive imaging modeillustrated in FIG. 15, the controller 40 is able to automaticallyacquire the type of the acoustic matching member 50 by employing animage imaged by the camera 39. In such cases, the medical imaging device10 needs to be equipped with the camera 39, and there is a concern thatthe camera 39 might break due to emission of the radiation R by theradiation emitter 25. Moreover, a process to image the marker 60 usingthe camera 39 is added in addition to imaging the radiographic image ofthe breast N using the radiation detector 30. Hence, as described above,the medical imaging device 10 preferably employs a radiographic imageimaged by the preshot for the controller 40 to automatically acquire thetype of the acoustic matching member 50.

The medical imaging devices 10 of the exemplary embodiments explainedabove include the press plate 32 for pressing the breast N and theradiation emitter 25 for radiating the radiation R onto the breast N,and are medical imaging devices capable of performing radiographicimaging and ultrasound imaging of the breast N. The controller 40 of themedical imaging device 10 acquires various information indicating thetype of the acoustic matching member 50 inserted between the press plate32 and the breast N in cases in which ultrasound imaging of the breast Nis being performed. Moreover, the controller 40 sets the tube voltage ofthe radiation emitter 25 to the first tube voltage in cases in whichradiographic imaging alone is being performed on the breast N, and setsthe tube voltage of the radiation emitter 25 to the second tube voltagethat is different from the first tube voltage by using the variousinformation acquired in cases in which radiographic imaging andultrasound imaging is performed on the breast N consecutively with theacoustic matching member 50 still inserted.

Thus, according to the medical imaging devices 10 of the above exemplaryembodiments, suitable radiographic imaging can be performed that takesinto consideration the type of the acoustic matching member 50 beingemployed.

Note that although in the above exemplary embodiments, the type of theacoustic matching member 50 is determined according to the thickness ofthe acoustic matching member 50 at a part through which the radiation Rpasses, the determination of the type of the acoustic matching member 50is not limited thereto. The type of the acoustic matching member 50 maybe determined according to the shape and material, etc. of the acousticmatching member 50, or may be determined according to factors thatinfluence the characteristics of radiation R passing through theacoustic matching member 50. The type of the acoustic matching member 50may also be categorized and set according to these factors. Note thatchanges to the characteristics of the radiation R depend particularly onthe thickness of the acoustic matching member 50, and so in cases inwhich the type of the acoustic matching member 50 is not determinedaccording to the thickness thereof, the controller 40 preferablyacquires the type and thickness of the acoustic matching member 50, andadjusts the tube voltage according to the type and thickness of theacoustic matching member 50.

Moreover, although in the above exemplary embodiments, the acousticmatching member 50 is only provided between the breast N and the pressplate 32 when performing radiographic imaging in the consecutive imagingmode, an acoustic matching member such as the echo jelly 52 may also beprovided on the upper face of the press plate 32 (the face on theopposite side to the face where the acoustic matching member 50 isprovided), or an acoustic matching member such as the echo jelly 52 mayonly be provided on the upper face of the press plate 32. In such cases,the tube voltage of the radiation tube 26 may be set according to thetype of all of the acoustic matching members provided.

Moreover, although in the above exemplary embodiments it is thecontroller 40 of the medical imaging device 10 that sets the tubevoltage and dose in cases in which radiographic imaging is performed inthe consecutive imaging mode, the setting may be performed by somethingother than the controller 40. For example, a tube voltage setting deviceprovided separately to the medical imaging device 10 may perform thesetting. FIG. 16 illustrates a block diagram of an example of aconfiguration of a medical imaging device 10 and a tube voltage settingdevice 80 in such a case. As illustrated in FIG. 16, the tube voltagesetting device 80 includes a controller 82, a storage unit 84, anoperation panel 86, and an I/F 88. The controller 82, the storage unit84, the operation panel 86, and the I/F 88 are connected together by abus 89, such as a system bus or a control bus, so as to be capable ofexchanging various signals with each other.

The controller 82 controls the overall operation of the tube voltagesetting device 80, and sets imaging conditions, such as the tube voltageand tube current, etc. in the radiation emitter 25 of the medicalimaging device 10. The controller 82 includes a CPU 82A, ROM 82B, andRAM 82C. Various programs, etc. to be executed by the CPU 82A arepre-stored in the ROM 82B. The RAM 82C temporarily stores various data.

The above-described tube voltage change table 42A and dose change table42B are stored in the storage unit 84. Hence, as illustrated in FIG. 16,the tube voltage change table 42A and the dose change table 42B are notstored in the storage unit 42 of the medical imaging device 10. Theoperation panel 86 is a touch panel or the like, and is employed when anoperator inputs information indicating the type of the acoustic matchingmember 50. The I/F 88 performs communication of various information withan external system (such as an RIS) or the like, and with the medicalimaging device 10 using wireless communication or wired communication.

The controller 82 of the tube voltage setting device 80 acquires variousinformation indicating the type of the acoustic matching member 50 thatis disposed between the ultrasound probe and the breast N duringultrasound imaging of the breast N, and that is present between theradiation emitter 25 and the breast N during radiographic imaging of thebreast N. Moreover, the controller 82 sets the tube voltage of theradiation tube 26 of the radiation emitter 25 according to the typeindicated by the acquired various information when performingradiographic imaging of the breast N. The controller 82 also sets thedose of the radiation R emitted from the radiation tube 26 of theradiation emitter 25 according to the type indicated by the acquiredvarious information.

The method employed by the controller 82 to set the tube voltage anddose may, for example, be similar to the method employed by thecontroller 40 of the medical imaging device 10 in the above exemplaryembodiments. For example, similarly to in the first exemplary embodimentas described above, information may be acquired indicating the type ofthe acoustic matching member 50 that has been input by an operator, andthe tube voltage and dose, which have been determined according to thetype of acoustic matching member 50 by employing the tube voltage changetable 42A and the dose change table 42B stored in the storage unit 84,may be set in the radiation emitter 25 through the I/F 88 and the I/F46. Moreover, similarly to in the second exemplary embodiment, theradiographic image 70 obtained by the preshot may be acquired from themedical imaging device 10, and the marker image 73 detected in theradiographic image 70, the information of the marker 60 acquired, andthe type of the acoustic matching member 50 acquired based on theinformation of the marker 60. Moreover, an image obtained by imaging themarker 60 using the camera 39 may be acquired from the medical imagingdevice 10, a marker image detected in the image, the information of themarker 60 acquired, and the type of the acoustic matching member 50acquired based on the information of the marker 60.

Note what is referred to as a console may be employed, or a dedicatedcontroller device for the radiation emitter 25, may be employed as sucha tube voltage setting device 80. Moreover, the tube voltage settingdevice 80 may be provided on the arm 20 of the medical imaging device10.

There are no particular limitations to the radiation R in the aboveexemplary embodiments, and X-rays, gamma rays, etc. may be employedtherefor.

The configuration, operation, and the like of the medical imaging device10, etc. explained in the above exemplary embodiments are merelyexamples thereof, and various modifications are possible according tothe circumstances within a range not departing from the spirit of theinvention.

An object of the present disclosure is to provide a medical imagingdevice, a tube voltage setting device, an imaging control method, and arecording medium storing an imaging control program capable ofperforming suitable radiographic imaging that takes into considerationthe type of acoustic matching member employed.

In order to achieve the above object, a medical imaging device of thepresent disclosure includes a press plate that presses a breast, anemitter that radiates radiation onto the breast, an acquisition sectionthat acquires various information indicating a type of an acousticmatching member inserted between the press plate and the breast in casesin which ultrasound imaging of the breast is performed, and a settingsection. The setting section sets a tube voltage of the emitter to afirst tube voltage in cases in which radiographic imaging of the breastis performed alone, and that sets the tube voltage of the emitter to asecond tube voltage different from the first tube voltage by employingthe various information acquired by the acquisition section in cases inwhich radiographic imaging and ultrasound imaging of the breast areperformed consecutively with the acoustic matching member stillinserted.

The setting section of the medical imaging device of the presentdisclosure may be configured to further set a dose of radiation emittedfrom a radiation tube of the emitter according to the type indicted bythe various information.

The setting section of the medical imaging device of the presentdisclosure may be configured to determine the dose to set based oninformation indicating a correspondence relationship between type of theacoustic matching member and dose of the radiation or correction valuesof the dose.

The medical imaging device of the present disclosure may be configuredsuch that the acoustic matching member is applied with a markercorresponding to the various information, the medical imaging devicefurther includes an imaging section that images the marker, and theacquisition section acquires the various information based on an imageof the marker imaged by the imaging section.

The medical imaging device of the present disclosure may be configuredsuch that the acoustic matching member is applied with a marker that hasa different transmissivity to radiation to that of the acoustic matchingmember and that corresponds to the various information, and theacquisition section radiates radiation from the emitter onto the markerand acquires the various information based on a radiographic image ofthe marker that has been imaged.

The medical imaging device of the present disclosure may be configuredsuch that the type of the acoustic matching member is determinedaccording to a thickness of a part of the acoustic matching memberthrough which radiation emitted from the emitter passes.

The setting section of the medical imaging device of the presentdisclosure may be configured to determine the tube voltage to set basedon information indicating a correspondence relationship between type ofthe acoustic matching member and a tube voltage of the radiation tube ora correction value of the tube voltage.

The medical imaging device of the present disclosure may be configuredsuch that the tube voltage or the correction value of the tube voltagemakes a half value layer of radiation passing through the acousticmatching member and incident to the breast the same as a half valuelayer of radiation not passing through the acoustic matching member andincident to the breast.

The medical imaging device of the present disclosure may be configuredsuch that, for cases in which radiographic imaging and ultrasoundimaging of the breast are performed consecutively with the acousticmatching member still inserted, in cases in which a different acousticmatching member to the acoustic matching member is further providedbetween the press plate and the emitter, the acquisition section furtheracquires various information indicating a type of the different acousticmatching member, and the setting section sets the tube voltage of theemitter using the various information of the acoustic matching memberand various information of the different acoustic matching memberacquired by the acquisition section.

The press plate of the medical imaging device of the present disclosuremay be configured to keep the breast in a pressed state until theradiographic imaging and ultrasound imaging have ended in cases in whichradiographic imaging and ultrasound imaging of the breast are performedconsecutively with the acoustic matching member still inserted.

In order to achieve the above object, a tube voltage setting device ofthe present disclosure includes: an acquisition section that acquiresvarious information indicating a type of an acoustic matching memberdisposed between an ultrasound probe and a breast in cases in whichultrasound imaging of the breast is performed, and present between aradiation emitter and the breast in cases in which radiographic imagingof the breast is performed; and a setting section that sets a tubevoltage of a radiation tube of the radiation emitter according to thetype indicated by the various information acquired by the acquisitionsection in cases in which radiographic imaging of the breast isperformed.

In order to achieve the above object, an imaging control method of thepresent disclosure is an imaging control method for a medical imagingdevice equipped with a press plate to press a breast and an emitter toradiate radiation onto the breast, and capable of performingradiographic imaging and ultrasound imaging of the breast. The imagingcontrol method includes: acquiring various information indicating a typeof an acoustic matching member inserted between the press plate and thebreast in cases in which ultrasound imaging of the breast is performed;setting a tube voltage of the emitter to a first tube voltage in casesin which radiographic imaging of the breast is performed alone; andsetting the tube voltage of the emitter to a second tube voltagedifferent from the first tube voltage by employing the acquired variousinformation in cases in which radiographic imaging and ultrasoundimaging of the breast are performed consecutively with the acousticmatching member still inserted.

In order to achieve the above object, a non-transitory recording mediumof the present disclosure stores a program that causes a computer toexecute an imaging control process for a medical imaging device equippedwith a press plate to press a breast and an emitter to radiate radiationonto the breast, and capable of performing radiographic imaging andultrasound imaging of the breast. The process includes: acquiringvarious information indicating a type of an acoustic matching memberinserted between the press plate and the breast in cases in whichultrasound imaging of the breast is performed; setting a tube voltage ofthe emitter to a first tube voltage in cases in which radiographicimaging of the breast is performed alone; and setting the tube voltageof the emitter to a second tube voltage different from the first tubevoltage by employing the acquired various information in cases in whichradiographic imaging and ultrasound imaging of the breast are performedconsecutively with the acoustic matching member still inserted.

The present disclosure can provide a medical imaging device, a tubevoltage setting device, an imaging control method, and a recordingmedium storing an imaging control program capable of performing suitableradiographic imaging that takes into consideration the type of acousticmatching member employed.

What is claimed is:
 1. An imaging control method for a medical imagingdevice that is equipped with a press plate to press a breast and anemitter to radiate radiation onto the breast, and that is capable ofperforming radiographic imaging and ultrasound imaging of the breast,the imaging control method comprising: acquiring information indicatinga type of an acoustic matching member inserted between the press plateand the breast in a case in which ultrasound imaging of the breast isperformed; setting a tube voltage of the emitter to a first tube voltagein a case in which radiographic imaging of the breast is performedalone; and setting the tube voltage of the emitter to a second tubevoltage that is different from the first tube voltage, by employing theacquired information, in a case in which radiographic imaging andultrasound imaging of the breast are performed consecutively with theacoustic matching member still inserted.
 2. The imaging control methodof claim 1, further comprising setting a dose of radiation emitted froma radiation tube of the emitter according to the type indicated by theinformation.
 3. The imaging control method of claim 2, wherein the doseof radiation is determined based on a correspondence relationshipbetween the type of the acoustic matching member and the dose ofradiation or correction values of the dose.
 4. The imaging controlmethod of claim 1, wherein: the acoustic matching member is applied witha marker corresponding to the information; the imaging control methodfurther includes imaging the marker; and the information is acquiredbased on an image of the marker that has been imaged.
 5. The imagingcontrol method of claim 1, wherein: the acoustic matching member isapplied with a marker that has a different transmissivity to radiationfrom that of the acoustic matching member and that corresponds to theinformation; and the information is acquired based on a radiographicimage of the marker that has been imaged by radiating radiation from theemitter onto the marker.
 6. The imaging control method of claim 1,wherein: the type of the acoustic matching member is determinedaccording to a thickness of a part of the acoustic matching memberthrough which radiation emitted from the emitter passes.
 7. The imagingcontrol method of claim 1, wherein: the tube voltage to be set isdetermined based on a correspondence relationship between the type ofthe acoustic matching member and a tube voltage of the radiation tube ora correction value of the tube voltage of the radiation tube.
 8. Theimaging control method of claim 7, wherein: the tube voltage or thecorrection value of the tube voltage makes a half value layer ofradiation passing through the acoustic matching member and incident tothe breast the same as a half value layer of radiation not passingthrough the acoustic matching member and incident to the breast.
 9. Theimaging control method of claim 1, wherein: for cases in whichradiographic imaging and ultrasound imaging of the breast are performedconsecutively with the acoustic matching member still inserted, and adifferent acoustic matching member from the acoustic matching member isfurther provided between the press plate and the emitter: the imagingcontrol method further comprises acquiring information indicating a typeof the different acoustic matching member; and the tube voltage of theemitter is set by using the information indicating the type of theacoustic matching member and the information indicating the type of thedifferent acoustic matching member, which have been acquired.
 10. Theimaging control method of claim 1, wherein: the press plate keeps thebreast in a pressed state until the radiographic imaging and theultrasound imaging have ended, in cases in which radiographic imagingand ultrasound imaging of the breast are performed consecutively withthe acoustic matching member still inserted.